Drug delivery device

ABSTRACT

Drug delivery devices, and methods of delivering pharmaceutically active agents to a target tissue within a body using such devices, are disclosed. One drug delivery device includes a body having an internal surface for placement proximate a target tissue and a well having an opening to the internal surface. An inner core comprising a pharmaceutically active agent is disposed in the well.

This application is a continuation of U.S. application Ser. No.10/186,960, filed Jul. 1, 2002, which is a continuation of U.S.application Ser. No. 09/660,000, filed Sep. 12, 2000, now U.S. Pat. No.6,413,540, which claims priority from U.S. Provisional Application No.60/160,673, filed Oct. 21, 1999.

FIELD OF THE INVENTION

The present invention generally pertains to biocompatible implants forlocalized delivery of pharmaceutically active agents to body tissue.More particularly, but not by way of limitation, the present inventionpertains to biocompatible implants for localized delivery ofpharmaceutically active agents to the posterior segment of the eye.

DESCRIPTION OF THE RELATED ART

Several diseases and conditions of the posterior segment of the eyethreaten vision. Age related macular degeneration (ARMD), choroidalneovascularization (CNV), retinopathies (i.e. diabetic retinopathy,vitreoretinopathy), retinitis (i.e. cytomegalovirus (CMV) retinitis),uveitis, macular edema, and glaucoma are several examples.

Age related macular degeneration (ARMD) is the leading cause ofblindness in the elderly. ARMD attacks the center of vision and blursit, making reading, driving, and other detailed tasks difficult orimpossible. About 200,000 new cases of ARMD occur each year in theUnited States alone. Current estimates reveal that approximately fortypercent of the population over age 75, and approximately twenty percentof the population over age 60, suffer from some degree of maculardegeneration. “Wet” ARMD is the type of ARMD that most often causesblindness. In wet ARMD, newly formed choroidal blood vessels (choroidalneovascularization (CNV)) leak fluid and cause progressive damage to theretina.

In the particular case of CNV in ARMD, two main methods of treatment arecurrently being developed, (a) photocoagulation and (b) the use ofangiogenesis inhibitors. However, photocoagulation can be harmful to theretina and is impractical when the CNV is near the fovea. Furthermore,photocoagulation often results in recurrent CNV over time. Oral orparenteral (non-ocular) administration of anti-angiogenic compounds isalso being tested as a systemic treatment for ARMD. However, due todrug-specific metabolic restrictions, systemic administration usuallyprovides sub-therapeutic drug levels to the eye. Therefore, to achieveeffective intraocular drug concentrations, either an unacceptably highdose or repetitive conventional doses are required. Periocularinjections of these compounds often result in the drug being quicklywashed out and depleted from the eye, via periocular vasculature andsoft tissue, into the general circulation. Repetitive intraocularinjections may result in severe, often blinding, complications such asretinal detachment and endophthalmitis.

In order to prevent complications related to the above-describedtreatments and to provide better ocular treatment, researchers havesuggested various implants aimed at localized delivery ofanti-angiogenic compounds to the eye. U.S. Pat. No. 5,824,072 to Wongdiscloses a non-biodegradable polymeric implant with a pharmaceuticallyactive agent disposed therein. The pharmaceutically active agentdiffuses through the polymer body of the implant into the target tissue.The pharmaceutically active agent may include drugs for the treatment ofmacular degeneration and diabetic retinopathy. The implant is placedsubstantially within the tear fluid upon the outer surface of the eyeover an avascular region, and may be anchored in the conjunctiva orsclera; episclerally or intrasclerally over an avascular region;substantially within the suprachoroidial space over an avascular regionsuch as the pars plana or a surgically induced avascular region; or indirect communication with the vitreous.

U.S. Pat. No. 5,476,511 to Gwon et al. discloses a polymer implant forplacement under the conjunctiva of the eye. The implant may be used todeliver neovascular inhibitors for the treatment of ARMD and drugs forthe treatment of retinopathies, retinitis, and CMV retinitis. Thepharmaceutically active agent diffuses through the polymer body of theimplant.

U.S. Pat. No. 5,773,019 to Ashton et al. discloses a non-bioerodablepolymer implant for delivery of certain drugs including angiostaticsteroids and drugs such as cyclosporine for the treatment of uveitis.Once again, the pharmaceutically active agent diffuses through thepolymer body of the implant.

All of the above-described implants require careful design andmanufacture to permit controlled diffusion of the pharmaceuticallyactive agent through a polymer body (matrix devices) or polymer membrane(reservoir devices) to the desired site of therapy. Drug release fromthese devices depends on the porosity and diffusion characteristics ofthe matrix or membrane, respectively. These parameters must be tailoredfor each drug moiety to be used with these devices. Consequently, theserequirements generally increase the complexity and cost of suchimplants.

U.S. Pat. No. 5,824,073 to Peyman discloses an indentor for positioningin the eye. The indentor has a raised portion that is used to indent orapply pressure to the sclera over the macular area of the eye. Thispatent discloses that such pressure decreases choroidal congestion andblood flow through the subretinal neovascular membrane, which, in turn,decreases bleeding and subretinal fluid accumulation.

Therefore, a need exists in the biocompatible implant field for asurgically implantable drug delivery device capable of safe, effective,rate-controlled, localized delivery of a wide variety ofpharmaceutically active agents to any body tissue. The surgicalprocedure for implanting such a device should be safe, simple, quick,and capable of being performed in an outpatient setting. Ideally, such adevice should be easy and economical to manufacture. Furthermore,because of its versatility and capability to deliver a wide variety ofpharmaceutically active agents, such an implant should be capable of usein clinical studies to deliver various agents that create a specificphysical condition in a patient or animal subject. In the particularfield of ophthalmic drug delivery, such an implantable drug deliverydevice is especially needed for localized delivery of pharmaceuticallyactive agents to the posterior segment of the eye to combat ARMD, CNV,retinopathies, retinitis, uveitis, macular edema, and glaucoma.

SUMMARY OF THE INVENTION

One aspect of the present invention comprises a drug delivery deviceincluding a body having an internal surface for placement proximate atarget tissue and a well having an opening to the internal surface. Aninner core comprising a pharmaceutically active agent is disposed in thewell.

In another aspect, the present invention comprises a method ofdelivering a pharmaceutically active agent to a target tissue within abody. A drug delivery device is provided. The drug delivery deviceincludes a body having an internal surface and a well having an openingto the internal surface, and an inner core disposed in the wellcomprising a pharmaceutically active agent. The device is disposedwithin the body so that the pharmaceutically active agent is incommunication with the target tissue through the opening.

In a further aspect, the present invention comprises an ophthalmic drugdelivery device including a body having a scleral surface for placementproximate a sclera and a well or cavity having an opening to the scleralsurface. An inner core comprising a pharmaceutically active agent isdisposed in the well.

In a further aspect, the present invention comprises a method ofdelivering a pharmaceutically active agent to an eye having a sclera. Adrug delivery device is provided. The drug delivery device includes abody having a scleral surface and a well having an opening to thescleral surface, and an inner core disposed in the well comprising apharmaceutically active agent. The device is disposed within the eye sothat the pharmaceutically active agent is in communication with thesclera through the opening.

In a further aspect, the present invention comprises a method ofdelivering a pharmaceutically active agent to an eye having a sclera, aTenon's capsule, and a macula. A drug delivery device comprising a bodyhaving a pharmaceutically active agent disposed therein is provided. Thedevice is disposed on an outer surface of the sclera, below the Tenon'scapsule, and proximate the macula.

BRIEF DESCRIPTION OF THE DRAWINGS

For a more complete understanding of the present invention, and forfurther objects and advantages thereof, reference is made to thefollowing description taken in conjunction with the accompanyingdrawings in which:

FIG. 1 is a side sectional view of a drug delivery device according to apreferred embodiment of the present invention;

FIG. 2 is a side sectional view of a second drug delivery deviceaccording to a preferred embodiment of the present invention;

FIG. 3 is a side sectional view schematically illustrating the humaneye;

FIG. 4 is detailed cross-sectional view of the eye of FIG. 3 along line4-4;

FIG. 5 is a perspective view of an ophthalmic drug delivery deviceaccording to a preferred embodiment of the present invention;

FIG. 6A is a side sectional view of the ophthalmic drug delivery deviceof FIG. 5;

FIG. 6B is an enlarged cross-sectional view of the ophthalmic drugdelivery device of FIG. 6A taken along line 6B-6B; and

FIG. 7 is a graphical illustration of the results of a pharmacokineticstudy with New Zealand White rabbits implanted with the ophthalmic drugdelivery device of FIGS. 5 through 6B showing the mean concentration ofa pharmaceutically active agent at a target site in the retina andchoroid of the rabbits as a function of time.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

The preferred embodiments of the present invention and their advantagesare best understood by referring to FIGS. 1 through 7 of the drawings,like numerals being used for like and corresponding parts of the variousdrawings.

FIG. 1 schematically illustrates a drug delivery device 10 according toa preferred embodiment of the present invention. Device 10 may be usedin any case where localized delivery of a pharmaceutically active agentto body tissue is required. By way of example, device 10 may be used totreat a medical disorder of the eye, ear, nose, throat, skin,subcutaneous tissue, or bone. Device 10 may be used in humans oranimals.

Device 10 generally includes a body 12 having an internal surface 14 andan external surface 16. As shown in FIG. 1, body 12 preferably has agenerally rectangular three-dimensional geometry with a proximal end 18and a distal end 20. Body 12 may have any other geometry that has aninternal surface 14 for placement proximate a target tissue in the bodyof a patient. By way of example, body 12 may have a cylindrical, anoval, a square, or other polygonal three-dimensional geometry.

Body 12 includes a well or cavity 22 having an opening 24 to internalsurface 14. An inner core 26 is preferably disposed in well 22. Innercore 26 is preferably a tablet comprising one or more pharmaceuticallyactive agents. Alternatively, inner core 26 may comprise a conventionalhydrogel having one or more pharmaceutically active agents disposedtherein. A retaining member 28 is preferably disposed proximate opening24. Retaining member 28 prevents inner core 26 from falling out of well22. When inner core 26 is a cylindrical tablet, retaining member 28 ispreferably a continuous rim or lip disposed circumferentially aroundopening 24 having a diameter slightly less than the diameter of tablet26. Alternatively, retaining member 26 may comprise one or more membersthat extend from body 12 into opening 24. Although not shown in FIG. 1,inner core 26 may alternatively comprise a suspension, solution, powder,or combination thereof containing one or more pharmaceutically activeagents. In this embodiment, internal surface 14 is formed withoutopening 24, and the suspension, solution, powder, or combination thereofdiffuses through the relatively thin portion of internal surface 14below inner core 26. Still further in the alternative, device 10 may beformed without well 22 or inner core 26, and the pharmaceutically activeagent(s) in the form of a suspension, solution, powder, or combinationthereof may be dispersed throughout body 12 of device 10. In thisembodiment, the pharmaceutically active agent diffuses through body 12into the target tissue.

The geometry of device 10 maximizes communication between thepharmaceutically active agent of inner core 26 and the tissue underlyinginternal surface 14. Internal surface 14 preferably physically contactsthe target tissue. By way of example, if the target tissue has agenerally flat surface, device 10 would be appropriate for the deliveryof a pharmaceutically active agent. As another example, if the targettissue has a generally convex surface, a device 10 a shown in FIG. 2having a generally concave internal surface 14 a designed to mate withsuch a target surface may be utilized. Corners 30 of proximal end 18 a,and corners 32 of distal end 20 a, may be slanted and/or rounded off tofacilitate surgical placement of device 10 a and to maximize comfort tothe patient. Retaining member 28 is preferably designed with a minimumthickness necessary to retain inner core 26 so as to dispose a surface26 a of inner core 26 in close proximity to the target tissue. Althoughnot shown in FIG. 1 or 2, inner core 26 may be formed so that surface 26a physically contacts the target tissue.

Alternatively, device 10 or 10 a may be disposed in the body of apatient so that internal surface 14 or 14 a is disposed proximate thetarget tissue. In this case, internal surface 14 or 14 a physicallycontacts intermediate tissue disposed between it and the target tissue.The pharmaceutically active agent of inner core 26 communicates with thetarget tissue through opening 24 and this intermediate tissue.

Referring again to FIG. 1, body 12 preferably comprises a biocompatible,non-bioerodable material. Body 12 more preferably comprises abiocompatible, non-bioerodable polymeric composition. Said polymericcomposition may be a homopolymer, a copolymer, straight, branched,cross-linked, or a blend. Examples of polymers suitable for use in saidpolymeric composition include silicone, polyvinyl alcohol, ethylenevinyl acetate, polylactic acid, nylon, polypropylene, polycarbonate,cellulose, cellulose acetate, polyglycolic acid, polylactic-glycolicacid, cellulose esters, polyethersulfone, acrylics, their derivatives,and combinations thereof. Examples of suitable soft acrylics are morefully disclosed in U.S. Pat. No. 5,403,901, which is incorporated hereinin its entirety by reference. Said polymeric composition most preferablycomprises silicone. Of course, said polymeric composition may alsocomprise other conventional materials that affect its physicalproperties, including, but not limited to, porosity, tortuosity,permeability, rigidity, hardness, and smoothness. Exemplary materialsaffecting certain ones of these physical properties include conventionalplasticizers, fillers, and lubricants. Said polymeric composition maycomprise other conventional materials that affect its chemicalproperties, including, but not limited to, toxicity, hydrophobicity, andbody 12—inner core 26 interaction. Body 12 is preferably impermeable tothe pharmaceutically active agent of inner core 26. When body 12 is madefrom a generally elastic polymeric composition, the diameter of well 22may be slightly less than the diameter of inner core 26. This frictionalfit secures inner core 26 within well 22. In this embodiment, body 12may be formed without retaining member 28, if desired.

Inner core 26 may comprise any pharmaceutically active agents suitablefor localized delivery to a target tissue. Examples of pharmaceuticallyactive agents suitable for inner core 26 are anti-infectives, including,without limitation, antibiotics, antivirals, and antifungals;antiallergenic agents and mast cell stabilizers; steroidal andnon-steroidal anti-inflammatory agents; combinations of anti-infectiveand anti-inflammatory agents; decongestants; anti-glaucoma agents,including, without limitation, adrenergics, β-adrenergic blockingagents, α-adrenergic agonists, parasypathomimetic agents, cholinesteraseinhibitors, carbonic anhydrase inhibitors, and prostaglandins;combinations of anti-glaucoma agents; antioxidants; nutritionalsupplements; drugs for the treatment of cystoid macular edema including,without limitation, non-steroidal anti-inflammatory agents; drugs forthe treatment of ARMD, including, without limitation, angiogenesisinhibitors and nutritional supplements; drugs for the treatment ofherpetic infections and CMV ocular infections; drugs for the treatmentof proliferative vitreoretinopathy including, without limitation,antimetabolites and fibrinolytics; wound modulating agents, including,without limitation, growth factors; antimetabolites; neuroprotectivedrugs, including, without limitation, eliprodil; and angiostaticsteroids for the treatment of diseases or conditions of the posteriorsegment of the eye, including, without limitation, ARMD, CNV,retinopathies, retinitis, uveitis, macular edema, and glaucoma. Suchangiostatic steroids are more fully disclosed in U.S. Pat. Nos.5,679,666 and 5,770,592, which are incorporated herein in their entiretyby reference. Preferred ones of such angiostatic steroids include4,9(11)-Pregnadien-17α,21-diol-3,20-dione and4,9(11)-Pregnadien-17α,21-diol-3,20-dione-21-acetate. Inner core 26 mayalso comprise conventional non-active excipients to enhance thestability, solubility, penetrability, or other properties of the activeagent or the drug core.

If inner core 26 is a tablet, it may further comprise conventionalexcipients necessary for tableting, such as fillers and lubricants. Suchtablets may be produced using conventional tableting methods. Thepharmaceutically active agent is preferably distributed evenlythroughout the tablet. In addition to conventional tablets, inner core26 may comprise a special tablet that bioerodes at a controlled rate,releasing the pharmaceutically active agent. By way of example, suchbioerosion may occur through hydrolosis or enzymatic cleavage. If innercore 26 is a hydrogel, the hydrogel may bioerode at a controlled rate,releasing the pharmaceutically active agent. Alternatively, the hydrogelmay be non-bioerodable but allow diffusion of the pharmaceuticallyactive agent.

Device 10 may be made by conventional polymer processing methods,including, but not limited to, injection molding, extrusion molding,transfer molding, and compression molding. Preferably, device 10 isformed using conventional injection molding techniques. Inner core 26 ispreferably disposed in well 22 after the formation of body 12 of device10. Retaining member 28 is preferably resilient enough to allow innercore 26 to be inserted through opening 24 and then to return to itsposition as shown in FIG. 1.

Device 10 is preferably surgically placed proximate a target tissue. Thesurgeon first makes an incision proximate the target tissue. Next, thesurgeon performs a blunt dissection to a level at or near the targettissue. Once the target tissue is located, the surgeon uses forceps tohold device 10 with internal surface 14 facing the target tissue anddistal end 20 away from the surgeon. The surgeon then introduces device10 into the dissection tunnel, and positions device 10 with internalsurface 14 facing the target tissue. Once in place, the surgeon may ormay not use sutures to fix device 10 to the underlying tissue, dependingon the specific tissue. After placement, the surgeon sutures the openingand places a strip of antibiotic ointment on the surgical wound.

The physical shape of body 12, including the geometry of internalsurface 14, well 22, opening 24, and retaining member 28, facilitate theunidirectional delivery of a pharmaceutically effective amount of thepharmaceutically active agent from inner core 26 to the target tissue.In particular, the absence of a polymer layer or membrane between innercore 26 and the underlying tissue greatly enhances and simplifies thedelivery of an active agent to the target tissue.

Device 10 can be used to deliver a pharmaceutically effective amount ofa pharmaceutically active agent to target tissue for many years,depending on the particular physicochemical properties of thepharmaceutically active agent employed. Important physicochemicalproperties include hydrophobicity, solubility, dissolution rate,diffusion coefficient, and tissue affinity. After inner core 26 nolonger contains active agent, a surgeon may easily remove device 10. Inaddition, the “preformed” tunnel facilitates the replacement of an olddevice 10 with a new device 10.

FIGS. 3 through 6B schematically illustrate an ophthalmic drug deliverydevice 50 according to a preferred embodiment of the present invention.Device 50 may be used in any case where localized delivery of apharmaceutically active agent to the eye is required. Device 50 isparticularly useful for localized delivery of active agents to theposterior segment of the eye. A preferred use for device 50 is thedelivery of pharmaceutically active agents to the retina proximate themacula for treating ARMD, choroidial neovascularization (CNV),retinopathies, retinitis, uveitis, macular edema, and glaucoma. Ofcourse, device 50 may also be utilized for localized delivery ofpharmaceutically active agents to body tissue other than the eye, ifdesired.

Referring first to FIG. 3, a human eye 52 is schematically illustrated.Eye 52 has a cornea 54, a lens 56, a sclera 58, a choroid 60, a retina62, and an optic nerve 64. An anterior segment 66 of eye 52 generallyincludes the portions of eye 52 anterior of a line 67. A posteriorsegment 68 of eye 52 generally includes the portions of eye 52 posteriorof line 67. Retina 62 is physically attached to choroid 60 in acircumferential manner proximate pars plana 70. Retina 62 has a macula72 located slightly lateral to its optic disk. As is well known in theophthahnic art, macula 72 is comprised primarily of retinal cones and isthe region of maximum visual acuity in retina 62. A Tenon's capsule orTenon's membrane 74 is disposed on sclera 58. A conjunctiva 76 covers ashort area of the globe of eye 52 posterior to limbus 77 (the bulbarconjunctiva) and folds up (the upper cul-de-sac) or down (the lowercul-de-sac) to cover the inner areas of upper eyelid 78 and lower eyelid79, respectively. Conjunctiva 76 is disposed on top of Tenon's capsule74. As is shown in FIGS. 3 and 4, and as is described in greater detailhereinbelow, device 50 is preferably disposed directly on the outersurface of sclera 58, below Tenon's capsule 74 for treatment of mostposterior segment diseases or conditions. In addition, for treatment ofARMD in humans, device 50 is preferably disposed directly on the outersurface of sclera 58, below Tenon's capsule 74, with an inner core ofdevice 50 proximate macula 72.

FIGS. 5, 6A, and 6B schematically illustrate drug delivery device 50 ingreater detail. Device 50 generally includes a body 80 having a scleralsurface 82 and an orbital surface 84. Scleral surface 82 is preferablydesigned with a radius of curvature that facilitates direct contact withsclera 58. Orbital surface 84 is preferably designed with a radius ofcurvature that facilitates implantation under Tenon's capsule 74. Body80 preferably has a curved, generally rectangular three-dimensionalgeometry with rounded sides 86 and 88, proximal end 90, and distal end92. As shown best in the side sectional view of FIG. 6A, orbital surface84 preferably has tapered surfaces 94 and 96 proximate proximal end 90and distal end 92, respectively, that facilitate sub-Tenon implantationof device 50 and enhance the comfort of the patient. Body 80 mayalternatively have a geometry similar to that of device 10 a shown inFIG. 2. In addition, body 80 may have any other geometry that has acurved scleral surface 82 for contact with sclera 58. By way of example,body 80 may have a generally cylindrical, oval, square, or otherpolygonal three-dimensional geometry.

Body 80 includes a well or cavity 102 having an opening 104 to scleralsurface 82. An inner core 106 is preferably disposed in well 102. Innercore 106 is preferably a tablet comprising one or more pharmaceuticallyactive agents. Alternatively, inner core 106 may comprise a conventionalhydrogel having one or more pharmaceutically active agents disposedtherein. A retaining member 108 is preferably disposed proximate opening104. Retaining member 108 prevents inner core 106 from falling out ofwell 102. When inner core 106 is a cylindrical tablet, retaining member108 is preferably a continuous rim or lip disposed circumferentiallyaround opening 104 having a diameter slightly less than the diameter oftablet 106. Alternatively, retaining member 108 may comprise one or moremembers that extend from body 80 into opening 104. Although not shown inFIG. 6A, inner core 106 may alternatively comprise a suspension,solution, powder, or combination thereof containing one or morepharmaceutically active agents. In this embodiment, scleral surface 82is formed without opening 104, and the suspension, solution, powder, orcombination thereof diffuses through the relatively thin portion ofscleral surface 82 below inner core 26. Still further in thealternative, device 50 may be formed without well 102 or inner core 106,and the pharmaceutically active agent(s) in the form of a suspension,solution, powder, or combination thereof may be dispersed throughoutbody 80 of device 50. In this embodiment, the pharmaceutically activeagent diffuses through body 80 into the target tissue.

The geometry and dimensions of device 50 maximize communication betweenthe pharmaceutically active agent of inner core 106 and the tissueunderlying scleral surface 82. Scleral surface 82 preferably physicallycontacts the outer surface of sclera 58. Although not shown in FIG. 6Aor 6B, inner core 106 may be formed so that surface 106 a physicallycontacts the outer surface of sclera 58. Alternatively, scleral surface82 may be disposed proximate the outer surface of sclera 58. By way ofexample, device 50 may be disposed in the periocular tissues just abovethe outer surface of sclera 58 or intra-lamellarly within sclera 58.

Body 80 preferably comprises a biocompatible, non-bioerodable material.Body 80 more preferably comprises a biocompatible, non-bioerodablepolymeric composition. The polymeric composition comprising body 80, andthe polymers suitable for use in the polymeric compositions of body 80,may be any of the compositions and polymers described hereinabove forbody 12 of device 10. Body 80 most preferably is made from a polymericcomposition comprising silicone. Body 80 is preferably impermeable tothe pharmaceutically active agent of inner core 106. When body 80 ismade from a generally elastic polymeric composition, the diameter ofwell 102 may be slightly less than the diameter of inner core 106. Thisfrictional fit secures inner core 106 within well 102. In thisembodiment, body 80 may be formed without retaining member 108, ifdesired.

Inner core 106 may comprise any ophthalmically acceptablepharmaceutically active agents suitable for localized delivery.Exemplary pharmaceutically active agents include the pharmaceuticallyactive agents listed hereinabove for inner core 26 of device 10. Innercore 106 may also comprise conventional non-active excipients to enhancethe stability, solubility, penetrability, or other properties of theactive agent.

If inner core 106 is a tablet, it may further comprise conventionalexcipients necessary for tableting, such as fillers and lubricants. Suchtablets may be produced using conventional tableting methods. Thepharmaceutically active agent is preferably distributed evenlythroughout the tablet. In addition to conventional tablets, inner core106 may comprise a special tablet that bioerodes at a controlled rate,releasing the pharmaceutically active agent. By way of example, suchbioerosion may occur through hydrolosis or enzymatic cleavage. If innercore 106 is a hydrogel, the hydrogel may bioerode at a controlled rate,releasing the pharmaceutically active agent. Alternatively, the hydrogelmay be non-bioerodable but allow diffusion of the pharmaceuticallyactive agent.

Device 50 may be made by conventional polymer processing methods,including, but not limited to, injection molding, extrusion molding,transfer molding, and compression molding. Preferably, device 50 isformed using conventional injection molding techniques as describedhereinabove for device 10.

Device 50 is preferably surgically placed directly on the outer surfaceof sclera 58 below Tenon's capsule 74 using a simple surgical techniquethat is capable of being performed in an outpatient setting. The surgeonfirst performs a peritomy in one of the quadrants of eye 52. Preferably,the surgeon performs the peritomy in the infra-temporal quadrant, about3 mm posterior to limbus 77 of eye 52. Once this incision is made, thesurgeon performs a blunt dissection to separate Tenon's capsule 74 fromsclera 58, forming an antero-posterior tunnel. Once the tunnel isformed, the surgeon uses forceps to hold device 50 with scleral surface82 facing sclera 58 and distal end 92 away from the surgeon. The surgeonthen introduces device 50 into the tunnel in a generally circular motionto position inner core 106 of device 50 generally above the desiredportion of retina 62. The surgeon then closes the peritomy by suturingTenon's capsule 74 and conjunctiva 76 to sclera 58. After closing, thesurgeon places a strip of antibiotic ointment on the surgical wound.Alternatively, the surgeon may suture proximal end 90 of device 50 tosclera 58 to hold device 50 in the desired location before closure ofthe tunnel.

In the case of ARMD in the human eye, the surgeon utilizes theabove-described technique to position inner core 106 of device 50 in oneof two preferred locations in the infra-temporal quadrant of eye 52. Onepreferred location is directly on the outer surface of sclera 58, belowTenon's capsule 74, with inner core 106 positioned proximate to, but notdirectly above, macula 72. A surgeon may position inner core 106 ofdevice 50 at this location by moving distal end 92 of device 50 belowthe inferior oblique muscle in a direction generally parallel to thelateral rectus muscle. A second preferred location is directly on theouter surface of sclera 58, below Tenon's capsule 74, with inner core106 positioned directly above macula 72. A surgeon may position innercore 106 of device 50 at this location by moving distal end 92 of device50 toward macula 72 along a path generally between the lateral andinferior rectus muscles and below the inferior oblique muscle. For ARMD,the pharmaceutically active agent of inner core 106 is preferably one ofthe angiostatic steroids disclosed in U.S. Pat. Nos. 5,679,666 and5,770,592.

The physical shape of body 80 of device 50, including the geometry ofscleral surface 82, well 102, opening 104, and retaining member 108,facilitate the unidirectional delivery of a pharmaceutically effectiveamount of the pharmaceutically active agent from inner core 106 throughsclera 58, choroid 60, and into retina 62. In particular, the absence ofa polymer layer or membrane between inner core 106 and sclera 58 greatlyenhances and simplifies the delivery of an active agent to retina 62.

It is believed that device 50 can be used to deliver a pharmaceuticallyeffective amount of a pharmaceutically active agent to retina 62 formany years, depending on the particular physicochemical properties ofthe pharmaceutically active agent employed. Important physicochemicalproperties include hydrophobicity, solubility, dissolution rate,diffusion coefficient, and tissue affinity. After inner core 106 nolonger contains active agent, a surgeon may easily remove device 50. Inaddition, the “pre-formed” tunnel facilitates the replacement of an olddevice 50 with a new device 50.

The following example illustrates effective drug delivery to a rabbitretina using a preferred embodiment and surgical technique of thepresent invention, but are in no way limiting.

EXAMPLE

A device 50 was surgically implanted on the outer surface of the sclera,below the Tenon's capsule, generally along the inferior border of thelateral rectus muscle of the right eye of twenty (20) New Zealand Whiterabbits using a procedure similar to that described hereinabove forimplantation of device 50 on sclera 58 of eye 52. Device 50 wasconstructed as shown in FIGS. 5 through 6B, with the followingdimensions. Body 80 had a length 110 of about 15 mm, a width 112 ofabout 7.0 mm, and a maximum thickness 114 of about 1.8 mm. Retainingmember 108 had a thickness 116 of about 0.15 mm. Scleral surface 82 hada radius of curvature of about 8.5 mm and an arc length of about 18 mm.Inner core 106 was a cylindrical tablet with a diameter of about 5.0 mmand a thickness of about 1.5 mm. Opening 104 had a diameter of about 3.8mm. Well 102 had a diameter of about 4.4 mm. The pharmaceutically activeagent used in tablet 106 was 4,9(11)-Pregnadien-17α,21-diol-3,20-dione,an angiostatic steroid sold by Steraloids, Inc. of Wilton, N.H., andwhich is more fully disclosed in U.S. Pat. Nos. 5,770,592 and 5,679,666.The formulation of tablet 106 consisted of 99.75 weight percent4,9(11)-Pregnadien-17α,21-diol-3,20-dione, and 0.25 weight percentmagnesium stearate.

At one week after implantation, 4 rabbits were euthanized and theirright eyes were enucleated. The device 50 was removed from the eyes, andthe location of tablet 106 was marked on their sclerae. Following theremoval of the anterior segment and the vitreous of each eye andinversion of the thus formed eye-cup, a 10 mm diameter circular zone ofretinal tissue, concentric with and below the location of tablet 106 onthe sclera, was harvested (the “target site”). A 10 mm diameter circularzone of retinal tissue was also harvested from a second site locatedremote from the target site and on the other side of the optic nerve. Inaddition, a 10 mm diameter circular zone of retinal tissue was harvestedfrom a third site located between the second site and the target site.Similar 10 mm diameter circular zones of choroidal tissue were alsoharvested at the target site, second site, and third site. All thesetissues were separately homogenized, and the concentration ofangiostatic steroid in each of these tissues was determined via anocular pharmacokinetic study using high performance liquidchromatography and mass spectrometry analysis (LC-MS/MS). This procedurewas repeated at 3, 6, 9, and 12 weeks after implantation.

FIG. 7 shows the mean concentration of4,9(11)-Pregnadien-17α,21-diol-3,20-dione in the retina and the choroidat the target site as a function of time. The “error bars” surroundingeach data point represent standard deviation. As shown in FIG. 7, device50 delivered a pharmaceutically effective and generally constant amountof 4,9(11)-Pregnadien-17α,21-diol-3,20-dione to the retina and thechoroid at the target site for a time period of up to twelve weeks. Incontrast, the levels of 4,9(11)-Pregnadien-17α,21-diol-3,20-dione in theretina and the choroid at the second and third sites were at or nearzero. Therefore, device 50 also delivered a localized dose ofangiostatic steroid to the retina and the choroid at the target site.

From the above, it may be appreciated that the present inventionprovides improved devices and methods for safe, effective,rate-controlled, localized delivery of a variety of pharmaceuticallyactive agents to any body tissue. The surgical procedure for implantingsuch devices is safe, simple, quick, and capable of being performed inan outpatient setting. Such devices are easy and economical tomanufacture. Furthermore, because of their capability to deliver a widevariety of pharmaceutically active agents, such devices are useful inclinical studies to deliver various agents that create a specificphysical condition in a patient or animal subject. In the particularfield of ophthalmic drug delivery, such devices are especially usefulfor localized delivery of pharmaceutically active agents to theposterior segment of the eye to combat ARMD, CNV, retinopathies,retinitis, uveitis, macular edema, and glaucoma.

It is believed that the operation and construction of the presentinvention will be apparent from the foregoing description. While theapparatus and methods shown or described above have been characterizedas being preferred, various changes and modifications may be madetherein without departing from the spirit and scope of the invention asdefined in the following claims.

1. An ophthalmic drug delivery device, comprising: a body having: ascleral surface having a radius of curvature that facilitates contactwith a sclera of a human eye; a well having an opening to said scleralsurface; and a geometry that facilitates disposing said device on anouter surface of said sclera, below a Tenon's capsule of said eye, andin a posterior segment of said eye; and an inner core disposed in saidwell and comprising a pharmaceutically active agent.
 2. The ophthalmicdrug delivery device of claim 1, wherein said body has a geometry thatfacilitates disposing said device on said outer surface of said sclera,below said Tenon's capsule, and in said posterior segment so that saidinner core is disposed proximate a macula of said eye.
 3. The ophthalmicdrug delivery device of claim 2, wherein said body has a geometry thatfacilitates disposing said device on said outer surface of said sclera,below said Tenon's capsule, and in said posterior segment so that saidinner core is disposed generally above said macula.
 4. The ophthalmicdrug delivery device of claim 1, wherein said inner core is a tablet. 5.The ophthalmic drug delivery device of claim 4, wherein at least aportion of said body is made from a generally elastic material so thatsaid generally elastic material, a geometry of said well, and a geometryof said tablet frictionally secure said tablet within said well.
 6. Theophthalmic drug delivery device of claim 4, wherein said tablet isformulated to bioerode and release said pharmaceutically active agent ata controlled rate.
 7. The ophthalmic drug delivery device of claim 1,wherein said inner core is a hydrogel.
 8. The ophthalmic drug deliverydevice of claim 7, wherein said hydrogel is formulated to bioerode andrelease said pharmaceutically active agent at a controlled rate.
 9. Theophthalmic drug delivery device of claim 7, wherein saidpharmaceutically active agent diffuses through said hydrogel at acontrolled rate.
 10. The ophthalmic drug delivery device of claim 1,further comprising a retaining member extending from said body proximatesaid opening, and wherein said retaining member helps to retain saidinner core in said well.
 11. The ophthalmic drug delivery device ofclaim 10, wherein said retaining member comprises a rim at leastpartially disposed around said opening.
 12. The ophthalmic drug deliverydevice of any one of claims 1-11, wherein said pharmaceutically activeagent comprises a compound selected from the group consisting of4,9(11)-Pregnadien-17α,21-diol-3,20-dione and4,9(11)-Pregnadien-17α,21-diol-3,20-dione-21-acetate.
 13. The ophthalmicdrug delivery device of any one of claims 1-11, wherein saidpharmaceutically active agent comprises eliprodil.